DE19919151A1 - Arrangement for scaleable multi-sectional computer tomography scanning enables selection of section thickness, images per rotation selection for axial scans, thickness, scan mode or scan speed for helical scans - Google Patents

Abstract

The arrangement has a user interface with selectable scan parameters for helical and axial scans, including section thickness for multi-sectional scans. There is a controller for the patient bed speed, a scan and reconstruction control unit connected to the bed speed controller, a multi-section detector connected to the control unit and a host computer with a monitor displaying the user interface via which the scan parameters can be selected. Independent claims are also included for a method of generating an image in a scaleable multi-sectional computer tomography system and for a host computer for use in the system.

Description

The present invention relates generally to a computer Tomography (CT) imaging and in particular a multi-section CT scanner with a scalable X-ray column limator, a scalable X-ray detection device device, a scalable X-ray data acquisition system, scalable scan data processing and scaling reconstructed scan image.

Typical CT patient scans are either in one axial mode (i.e., the patient table stops scanning is executed and then the patient table moves the next location) or in a spiral mode (i.e., the pati duck table moves continuously during scanning) executed. Single cut scanners are common and dual (2) slice CT systems are known. At least some of the commercially available dual cut systems have some Restrictions on. In general, when performing such scans compromise between patients scanning speed, image quality and X-ray tube loads are closed. For example, The pati may get an improved image quality duck scanning speed reduced or the x-ray tubes load can be increased, or both. An increase in pati duck scanning speed may deteriorate Image quality result or an increased X-ray tube loading Require service, or both. So far, none offers known system the advantages of an increased patient keying speed, improved image quality and decrease X-ray tube exposure.  

Furthermore, the well-known dual cut commercially available systems not scalable, d. H. such dual cut systems cannot capture more than two sections of Data can be configured. So far, nothing known System an operator the selection of the section thickness and number of images per revolution for axial scans and the Section thickness, scanning mode and scanning speed for spiral scanning.

The invention is therefore based on the object, the first to solve the problems listed.

According to the invention, these problems are solved by a scalable Multi-cut system solved that according to an embodiment a scalable multi-cut detection device, a ska scalable data acquisition system (SDAS), scalable Ab Touch management, control and image reconstruction processes and has scalable image display and analysis. Of the The term "scalable" generally means here that a Operator the desired number of cuts and the cut thickness for images to be displayed easily and simply can choose. With this multi-cut system, many rows can of X-ray scan data can be detected. Also be an increased patient scanning speed, an improved one Image quality and a reduced X-ray tube exposure enough.

In the axial multi-slice scanning mode, before the image construction many rows of sample data are processed, and the data can be used to generate either a variety thin cuts or a reduced number of thick cuts te with reduced image artifacts. Furthermore  can retrospectively view images with thicker slices into thinner slices of images based on clinical slide gnose requirements can be reconstructed. As a result the number of unwanted pictures for viewing, filming and Archiving reduced. Images with high z- Reconstruct axis resolution later for patient diagnosis be.

In the spiral multi-cut scan mode, multiple enable Combinations of patient table speed and X-ray beam and detector collimations generation of images with different z-axis resolution. At for example at a table speed of 30 mm / rotation images of 5-10 mm cuts are generated. Bil those with thicker cuts (such as 10 mm) be generated with foresight, which is the advantage of a reduced number of images and a reduced image re construction time results. Later, images can be made thinner Cut retrospectively using the same data be generated. Such thinner sectional images can be found in Ab depending on clinical application requirements to be such. Such thinner sectional images can be used without it generate a new scan of the patient.

The invention is described below with reference to exemplary embodiments len with reference to the accompanying drawing wrote. Show it:

Fig. 1 is a pictorial view of a CT imaging system,

Fig. 2 is a schematic block diagram of the presented in FIG. 1 Darge system,

Fig. 3 shows an embodiment of a sample user interface that can be used in connection with the illustrated in FIGS. 1 and 2 system,

Fig. 4 is a perspective view of a CT system detector array,

Fig. 5 is a perspective view of a ge in Fig. 4 showed acquisition module,

Fig. 6 shows the geometric construction of the shown in FIG. 1, the CT system,

Fig. 7 is a schematic representation of gungs- Röntgenstrahlerzeu and sensing components viewed from a side of a gantry,

Fig. 8A, 8B and 8C the operation of a comb-collimator in the example shown in Fig. 1 CT system and

FIG. 9A, 9B and 9C schematically illustrate the detection of Abtastda th for different average numbers and slice thicknesses.

In Fig. 1, a computer tomography (CT) imaging system 10 is shown according to an embodiment, which includes a barrel bearing 12 , which is a third-generation CT scanner. The barrel bearing 12 has an X-ray source 14 , which projects X-rays in the direction of a detection array 16 on the opposite side of the barrel bearing 12 . The detection array 16 consists of a plurality of detection modules, which together detect the projected X-rays that fall through a medical patient 18 . Each detection module generates an electrical signal that represents the intensity of an incident X-ray beam and thus the attenuation of the beam when it falls through the patient 18 .

During a scan for recording X-ray beam projection data, the barrel bearing 12 and the components attached to it rotate about a center of rotation. A motorized table 20 positions the patient 18 relative to the barrel bearing 12 . In particular, the table 20 moves portions of the patient 18 through a barrel bearing opening 22 during a scan.

The system hardware architecture, ver different scanning modes and an example of a user interface place described.

System hardware architecture

FIG. 2 shows a schematic block diagram of the system shown in FIG. 1. Referring to FIG. 2, the system 10 includes egg NEN host computer 24 which is connected to a monitor or screen 26 for displaying images and messages to an operator. The computer 24 is also connected to a keyboard 28 and a mouse 30 to enable the operator to enter information and commands for the computer 24 . The computer 24 is connected to a scan and reconstruction control unit (SRU) 32 . The SRU 32 also includes imaging controls. According to a specific exemplary embodiment, the SRU 32 contains a PCI-based SGI central processing unit which operates on an IRIX operating system. The SRU 32 also includes an interface processor for interfacing with the data acquisition system (described below) and a known scan data correction digital signal processing board for performing preprocessing. The SRU 32 also includes an imaging device for known filtered back-projection and post-processing operations.

A stationary control device 34 is connected to the SRU 32 and to a table control device 36 . The stationary control device 34 is also connected via a contact ring 38 to an on-board control device 40 and a scalable data acquisition system (SDAS) 42 . The contact ring 38 enables the contactless transmission of signals via the contact ring limitation and supports the bandwidth required for the transmission of data and commands via the limitation. The SDAS 42 samples data from the detection device 16 and detects it and converts the sampled analog signals into digital signals. The SDAS 42 in the particular embodiment includes 48 interchangeable transducer cards to support four-row data acquisition. 24 cards can be used for two-row data acquisition. In this embodiment, there are 64 input channels per converter card, and a 1408 Hz scan can be performed. The SDAS 42 also includes an initial preamplifier to amplify the signals. Forward error correction is applied to the output data.

The on-board control device 40 controls the operation of the X-ray source 14 and the operation of the SDAS 42 , which converts analog signals into digital data as stated above. The x-ray source 14 includes a high voltage generator 44 connected to an x-ray tube 46 . Tube 46 may be, for example, a known tube, such as the Gemini-1 tube, which is currently used in at least some commercially available CT systems from General Electric Company, Milwaukee, WI, 53201. Beams projected through the x-ray tube 46 pass through a comb collimator 48 in front of the patient and strike the detector 16 (which is shown as a 16-row detector). The comb collimator 48 is also controlled by the onboard controller 40 . Output signals of the detection device 16 are fed to the SDAS 42 .

In FIG. 2, operation of the system control flow is real time shown by thick lines 10 of the data flow, the control by normal lines and by broken lines regard. The reference numerals associated with the rivers are listed below:

Reference list

1

Scanning and reconstruction instructions from the operator

2nd

Sampling rule for "master" control device

3rd

Sampling parameters spread over

3rd

a table position

3rd

bRotation parameters

3rd

ckV and mA selection

3rd

d X-ray collimation and filter selection

3rd

eCoder slice thickness and SDAS gain selection

4th

Real time control signals during the scan

5

High voltage

6

non-collimated x-ray

7

collimated x-ray

8th

analog sample data

9

digital scan data

10th

Patient images

The rotation of the barrel bearing 12 and the operation of the X-ray source 14 are generally controlled by the controller 34 . The on-board control device 40 , which is under the control of the stationary control device 34 , supplies the X-ray source 14 with energy and time signals. The SDAS 42 samples analog data from the detection device 16 and converts the data into digital signals for subsequent processing. The SRU 32 receives sampled and digitized x-ray data from the SDAS 42 and performs image reconstruction at high speed. The reconstructed image is fed to the computer 24 as an input signal which stores the image in a mass storage device.

Computer 24 also receives commands and scanning parameters from an operator via keyboard 28 and mouse 30 . The monitor 26 enables the operator to view the reconstructed image and other data from the computer 24 . The commands and parameters supplied by the operator are used by the computer 24 to form control signals and information. In addition, the control device 36 controls the motorized table 20 for positioning the patient 18 ( FIG. 1).

Scan modes

In general, the CT system described above is Er Collection of incision, two-cut or multi-cut data operable. The system can perform axial and helical scanning conditions are carried out, and cross-sectional images can be made nes scanned object processed, reconstructed, attached shows and / or archived. A scalable axial Image reconstruction and display relates, for example on the selectability of the image thickness, the number of cuts and the number of images to display. Furthermore, that is System is not based on a specific image reconstruction algo rithmus limited and many different recon structural algorithms are used. Example algorithms are in US-A-5 469 487, US-A-5 513 236, US-A-5 541,970, US-A-5 559 847 and US-A-5 606 585 and in pending U.S. patent applications 08/561382 (filed on May 21, November 1995), 08/779961 (filed December 23, 1996) and 08/797101 (filed November 26, 1997).

Many rows can be made in the axial multi-cut scanning mode of scan data before image reconstruction is processed the, and the data can either be used to generate a lot number of thin cuts or a reduced number of thick ones Cuts with reduced image artifacts can be used. You can also use images with thicker sections later based retrospectively on thinner slices of images clinical diagnostic requirements are reconstructed. Info the number of unwanted pictures is viewed for viewing, Filming and archiving reduced. In addition, Bil the one with high z-axis resolution later for patient diagnosis be reconstructed.  

Examples of axial multi-cut modes are given below in Ta belle 1 cited.

Table 1

According to a particular example, there is an Mo for an axial dus capture for a 2.5 mm image thickness in 2i mode several selectable retrospective reconstruction options. Example Four images can be cut with a section thickness of 1.25 mm be reconstructed, two images with a section thickness of 2.5 mm can be reconstructed, and an image with a Section thickness of 5 mm can be reconstructed.  

Accordingly, multiple images (e.g. four images) reconstructed retrospectively with a thinner section are considered to be in the mode (i.e. 2i) in which the scan was carried out. Also, fewer pictures can be taken (for example an image) with a thicker section thickness be reconstructed retrospectively than in the mode in which the scan was performed.

The system also enables archiving storage of fewer images, the less Need space. For example, if a Pati duck anatomy can be scanned in the 2i mode, 80 Images are generated. The storage of 80 pictures for egg ne patient anatomy of 20 mm requires a high storage capacity capacity. It is often the case that high resolution is not required for the entire 20 mm of patient anatomy are. For example, it may be the case that only un about 5 mm of the anatomy require such a high resolution. Using the 2.5 mm 2i mode scan Thickness captured data allows the operator to create images with a thickness of 5 mm for the main part of the anatomy and thinner image cuts (e.g. 1.25 mm) only reconstruct at the locations where a higher resolution is required. Under Ver This retrospective reconstruction can use the number images to be archived are noticeably reduced.

The retrospective reconstruction described above will trained via the user interface and enables da the scan data using a multi-slice Detection device can be detected, which below Licher is described. If the scan data for thin Cuts are available, the operator can choose from a variety  different cutting thicknesses when performing the retro Select spective reconstruction.

In the spiral multi-cut scan mode, multiple enable Combinations of patient table speed and X-ray gene beam and detector collimations images with different z-axis resolution. For example, at a table speed of 30mm / rotation images can be created with 5-10mm cuts. Bil those with thicker cuts (such as 10 mm) can be foresighted are generated, from which the advantage of a reduced Number of images and a reduced image reconstruction time results. Later, thinner sectional images can be viewed retrospectively generated using the same data. This thinner slices may vary depending on clinical use requirements may be required. Such thinner Cross-sectional images can be taken without rescanning the patient be fathered.

Examples of spiral multi-cut modes are given below in Ta belle 2 listed.

Table 2

For example, in a high quality image (Hi-Q) - 3.75mm / rotation scan mode (i.e., the patient table be moves 3.75 mm with each barrel bearing rotation) or in one High-speed (Hi-Speed) scanning mode of 7.5 mm / rotation Images with section thicknesses of 1.25 mm and 2.5 mm retrospectively be reconstructed. As with the axial multi-cut mode are many alternatives depending on the particular order construction of the system components possible. Again, one of the like flexibility in retrospective reconstruction many benefits including using images the required resolution even when reducing the Storage of the desired images required memory capacity.

Example of a user interface

FIG. 3 shows an embodiment of a scan user interface that can be used in conjunction with the system shown in FIGS . 1 and 2. The interface may be implemented in a command set stored in host computer 24 ( FIG. 2) and displayed on the host computer monitor. At the scanning user interface, an operator can select the scanning mode, ie helical or axial scanning, as well as various scanning parameters associated with each mode. The selection can be made by the user, for example, simply by touching the desired range corresponding to the desired parameters. Touch-sensitive interfaces are known. Of course, other types of interfaces can also be used, and the interface shown in FIG. 3 is only one example of an interface.

In the spiral mode, the operator selects the desired cut thickness, the scanning mode and the scanning speed. The Hi-Q scanning corresponds to high picture quality scanning and the hi-speed scan corresponds to a fast patient table speed as described above in connection with Table 2 is described. For axial scanning, choose the operator the desired section thickness and the number of images to be generated per rotation.

So far, no multi-slice CT system offers scalable Ab Touch management, control and image reconstruction processes and a scalable image display and analysis like this system. In the present system, an operator can easily and simply the desired number of cuts and select the slice thickness for images to be displayed. Au In addition, an increased patient scanning speed, an improved image quality and a reduced X-ray tube renal load reached.

Additional component details

Below are examples of scalable multi-slice CT System components according to an embodiment described ben. Although certain component details are shown below are, of course, many alternative designs games possible. For example, although a certain solution device is described, can of course also others re detection devices in connection with the system ver be applied. The invention is not specific Detector type limited. In particular includes the detector described below is a lot  number of modules, each module having a large number of contains solution cells. Instead of the one described below certain detection device can be a detection direction, the non-segmented cells along the z-axis has, and / or a detection device that a variety of modules with many elements along the x-axis and / or the z-axis, in any direction for simultaneous Collect scalable multi-cut scan data together be applied.

Referring to FIGS. 4 and 5, the detection device 16 includes a plurality of detection modules 50th Each detection module 50 is attached to a detector housing 52 by plates 54 . Each module contains a multidimensional scintillator array 56 and a high density semiconductor array (not visible). A collimator (not shown) after the patient is located above and adjacent to the scintillator array 56 for collimating x-rays before these rays hit the scintillator array 56 . The scintillator array 56 contains a plurality of scintillation elements arranged in an array, and the semiconductor array contains a plurality of photodiodes arranged in an identical array. The photodiodes are deposited on a substrate 58 and the scintillator array 56 is over and attached to the substrate 58 .

Switching and decoding devices 60 are connected to the photodiode array. The photodiodes are torarray with the Szintilla 56 optically coupled and have electrical output lines from the transmission of signals, which constitute the signal output by scintillator array 56 light. In particular, each photodiode generates a separate low level analog output signal that is a measure of beam attenuation for a particular scintillator of the scintillator array 56 . The photodiode output lines extend from opposite sides of the semiconductor or photodiode array and are connected to the respective device 60 (for example by wire bonding).

The switching device 60 is a multi-dimensional semiconductor switching array similar in size to the photodiode array, and the switching device 60 is connected in an electrical circuit between the semiconductor array and the SDAS 42 ( FIG. 2). According to one embodiment, the device 60 contains a plurality of field effect transistors (FETs) which are arranged as a multidimensional array. Each field effect transistor includes an input line which is electrically connected to a respective photodiode output line, an output line and a control line (not shown). The FET output and control lines are electrically connected to the SDAS 42 via a flexible electrical cable 62 . In particular, approximately one half of the photodiode output lines are electrically connected to the respective FET input line on one side of the array, the other half of the photodiode output lines being electrically connected to the FET input lines on the other side of the array.

The decoder controls the operation of the field effect transistors to enable, disable, or combine the photodiode outputs in accordance with a desired number of cuts and cut resolutions for each cut. The decoding device is in one embodiment, for example, a known decoder chip or a known FET control device, and the decoding device includes a plurality of output and control lines which are connected to the field effect transistors and the SDAS 42 . In particular, the decoder outputs are electrically connected to the switching device control lines in order to enable the field effect transistors to transmit the correct data. The decoder control lines are electrically connected to the FET control lines and determine which outputs are released. Using the decoding device, certain field effect transistors are released, blocked, or their outputs combined, so that certain photodiode outputs are electrically connected to the SDAS 42 . Further details of the detection device 16 are described in the applicant's pending US patent application entitled "Photodiode Array For A Scalable Multislice Scanning Computed Tomography System".

According to a specific exemplary embodiment, the detection device 16 contains 57 detection modules 50 . The semiconductor array and the scintillator array 56 each have an array size of 16 × 16. Accordingly, the detector 16 has 16 rows and 912 columns (16 × 57 modules), which means that it captures 16 simultaneous cuts of data each time the barrel is rotated 12 allows. Of course, the invention is not limited to any particular array size, and the array can be larger or smaller depending on certain operator requirements. Likewise, the detection device 16 can work with many different section thicknesses and number modes, for example with one, two and four section modes. For example, the field effect transistors in the four-section mode can be configured such that data for four sections are acquired from one or more rows of the photodiode array. Depending on the particular structure of the field effect transistors as defined by the decoder control lines, various combinations of the photodiode outputs can be enabled, blocked or combined in such a way that the section thickness for example 1.25 mm, 2.5 mm, 3.75 mm or 5 mm. Other examples include a one-cut mode that includes a cut with cuts from 1.25 mm thick to 20 mm thick and a two-cut mode that contains two cuts with cuts from 1.25 mm thick to 10 mm thick. Other modes are also possible.

Fig. 6 shows the geometric structure of the CT system shown in Fig. 1 Darge and shows the Fasslagerkoordinatensy stem. The coordinate system is referred to in the following figures, and is used only for the description. In particular, the x-axis relates to an axis tangential to the turning circle of the drum bearing 12 . The y-axis refers to the radial axis extending from the isocenter (ISO) of the barrel bearing 12 in the direction of the X-ray tube focal point. The z-axis is the longitudinal axis (inside / outside) with respect to the scanning plane. The patient is moved along the z-axis on the patient table 20 during the scan.

According to FIG. 7, data are collected at different z-axis locations in a multi-section scanning. Fig. 6 shows a schematic representation of the system 10 when it is viewed from a side of the gantry 12.. The X-ray tube 46 contains an anode / target 64 and a cathode 66 . An uncollimated x-ray 68 is emitted through tube 46 and passes through comb collimator 48 . The collimator 48 includes a bow ("bowtie") filter 70 and tungsten combs 72 . As described above in connection with FIG. 2, the position of the combs 72 is controlled by the on-board control device 40 , which receives its commands from the host computer 24 via the SRU 32 and the stationary control device 34 . Stepper motors are connected, for example, to the combs 72 for precisely controlling the position of the combs 72 . The combs 72 of the comb collimator 48 can be set up independently with regard to the distance between the combs 72 and their location relative to the center of the collimator opening, depending on the data acquisition mode selected by the user.

A collimated x-ray beam 74 is emitted by the comb collimator 48 and the beam 74 passes through the patient 18 ( FIG. 1) and strikes the detection device 16 . As described above, the detector 16 includes a collimator 76 , a scintillator array 56, and a photodiode / switch array 78 (the photodiode and switch arrays are shown as one unit in FIG. 7, but can also be as described above separate arrays).

The output signals of the array 78 are fed to the SDAS 42 for processing via a flexible cable.

The following description relates to the operation of the comb collimator 48 and the detection device 16 to form a scalability in the number of cuts and the section thickness. Although the operation of the comb-collimator 48 and the operation of the detecting means 16 are sometimes described separately herein, is to be understood that the collimator 48 and the detector 16 together BEITEN ar to form the desired section number and slice thickness.

Figures 8a, 8b and 8c illustrate the operation of the comb collimator 48. Figure 8a shows the comb collimator 48 which is used to emit a centered, wide beam (e.g. a beam for obtaining four data cuts with a 5 mm -Section thickness) is set up. For a narrow centered beam, combs 72 , as shown in FIG. 8b, are moved inwardly an equal amount relative to the center of beam 68 . For example, the comb collimator configured as shown in FIG. 9 can be used to obtain four data slices with a slice thickness of 1.25 mm.

Collimator 48 can also be used to accommodate a z-axis beam shift that can occur during tube 46 operation. In particular, the combs 72 according to FIG. 8c can be positioned at uneven distances from the blasting center point 68 , as is indicated by the arrow labeled "comb offset". By the displacement or displacement of the combs 72 , as is shown in FIG. 8c, the beam 74 is displaced, as is indicated by the arrow labeled "beam displacement".

As described in more detail below, by controlling the position and width of the beam 74 on the comb collimator 48, scans can be performed to obtain data for many different slice numbers and slice thicknesses. For example, Fig. 9a corresponds to a selected detector structure when it is desired to obtain four data slices with a slice thickness of 5.0 mm. The combs 72 are widely separated in the z-axis direction to achieve 20 mm collimation, and the photodiode outputs are combined into four separate cuts by the switching array 78 . In particular, each data cut combines the outputs of four photodiodes into one signal ( 1 A, 2 A, 1 B and 2 B), and each cut data signal ( 1 A, 2 A, 1 B and 2 B) is sent to the SDAS 42 via the supplied flexible cable 62 .

For four data slices with a slice thickness of 1.25 mm, the detector arrangement shown in FIG. 9b can be used. In particular, the combs 72 are not separated from one another as much as for the 5.0 mm section thickness ( FIG. 9a). Rather, the combs 72 are separated in the z-axis direction to form a 5 mm collimation, and the photodiode outputs are combined by the switching array 78 into four separate cuts. In particular, each data combining section, the outputs of one photodiode into one signal (1 A, 2 A, 1 B and 2 B), and each section of the data signal (1 A, 2 A, 1 B and 2B) is supplied to the SDAS 42 via the flexible cables 62 fed.

Of course, many other combinations of number of cuts and thickness of cut are possible using system 10 . For example, according to FIG. 9c, for two data cuts with a 1.25 mm section thickness, the ridges 72 are separated or spaced in the z-axis direction to form a 2.5 mm collimation. The switching array 78 combines the photodiode outputs into two separate cuts. In particular, each data cut combines the outputs of a photodiode into one signal ( 1 A and 1 B), and each cut data signal ( 1 A and 1 B) is fed to the SDAS 42 via the flexible cables 62 . By controlling the comb collimator 48 and the channel summation along the z-axis as described above, scan data for many different cutting numbers and cutting thicknesses can be collected.

The system described above can be used in a number of ways be modified. For example, a graphics-based User interface to be used by the user simple prescription of multi-section scanning and image re construction in various forms, for example with egg optimal table speed, X-ray collimation, Data acquisition slice thickness, X-ray voltage and current values, as well as the reconstruction procedure for obtaining desired image quality. Such Interface can be through a touch screen, through who activates the voice or other interface methods those that are easy to use and understand. The host- Computer can be based on containing various default modes Based on the type of scan performed for further simplification programmed by the operator be. The multi-slice CT system described above can to capture one, two or more sections of Da used to develop increased flexibility become. This system also enables a high scan rate speed with good image quality and z-axis resolution with low X-ray tube exposure. Furthermore, the operator using the multi-slice scanning and Prescribe image reconstruction parameters easily and quickly.

According to the invention, a scalable multi-cut system is open beard, which according to one embodiment is scalable Multi-cut detection device, a scalable data acquisition system (SDAS), scalable scan management  Control and image reconstruction operations and a scaling includes image display and analysis. In an axial Multi-cut scan mode can have multiple rows of scan data processed before image reconstruction, and the data can produce either a variety of thin cuts or a reduced number of thick cuts with right induced image artifacts can be used. You can also Images with thicker slices later retrospectively in thin Other image slices based on clinical diagnostic requirements be reconstructed. As a result, the number is not wanted images for viewing, filming and archiving decreased. In addition, images with high z-axis Resolution later reconstructed for patient diagnosis. In a spiral multi-cut scan mode, a lot is possible number of combinations of patient table speed and X-ray and detector collimations that Creation of images with different z-axis Resolution. For example, at a table speed 30 mm / rotation Images from 5 mm to 10 mm sections be fathered. Thicker cutting patterns (such as 10 mm) can be generated with foresight, which is the benefit a reduced number of images and a reduced Image reconstruction time results. Later, thinner ones Cross-sectional images retrospectively using the same Da ten are generated. Such thinner sectional images can be found in Depends on the clinical application requirements to be demanding. These thinner sectional images can be made without it generate a new scan of the patient.

Claims (35)

1. User interface in a scalable multi-section computer tomography system ( 10 ) to enable a user to select scanning parameters, with selectable scanning parameters for helical and axial scans, the scanning parameters comprising section thicknesses for multi-section scans . 2. User interface in a scalable multi-section computer tomography system ( 10 ) with a table control device ( 36 ) for controlling the speed of a patient table ( 20 ), a scanning and reconstruction control unit ( 32 ) which is connected to the table control device , a multi-section detection device ( 16 ) connected to the control unit ( 32 ) and a host computer ( 24 ) with a monitor ( 26 ) which is programmed to train the user interface on the monitor, which is designed for this purpose, one Allow users to select scan parameters and include selectable scan parameters for wen del and axial scans, where the scan parameters include slice thicknesses for multi-slice scans, and where the scan parameters selected at the user interface are fed to the controller to control a scan. 3. User interface in a scalable multi-section computer tomography system ( 10 ) to enable a user to select scanning parameters, with selectable scanning parameters for helical scans, the scanning parameters comprising section thicknesses for multi-section scans. 4. User interface according to one of claims 1 to 3, the scan parameters for helical scan further include a scan speed. 5. User interface according to one of claims 1 to 3, the scanning parameters for the helical scan one Include high image quality scanning mode. 6. User interface according to one of claims 1 to 3, the scanning parameters for the helical scan one Include high speed scanning mode. 7. User interface according to one of claims 1 to 3, the scanning parameters for the helical scan an Ab scanning speed, a high image quality scanning mode and include a high speed scan mode. 8. User interface according to claim 1 or 2, wherein  the scanning parameters for the axial scanning also an on number of frames per rotation. 9. User interface in a scalable multi-section computer tomography system ( 10 ) to enable a user to select scanning parameters, with selectable scanning parameters for axial scans, the scanning parameters comprising section thicknesses for multi-section scans. 10. User interface according to claim 9, wherein the Ab keying parameters for the axial scanning also a number of Include images per rotation. 11. Host computer ( 24 ) for a multi-section computed tomography scanning system ( 10 ), which has a scanning and reconstruction control unit ( 32 ), with a user interface with selectable scanning parameters for helical and axial scans, the scanning parameters being cutting thicknesses for Include multiple slice scans. 12. The host computer of claim 11, wherein the sampling para meters for the helical scan also a scanning speed include. 13. The host computer of claim 11, wherein the sampling para meters for the spiral scanning a high image quality Include scan mode. 14. The host computer of claim 11, wherein the sampling para a high-speed Include scan mode.   15. The host computer of claim 11, wherein the sampling para a scanning speed for the helical scan, ei high picture quality scanning mode and high speed speed scanning mode. 16. The host computer of claim 11, wherein the sampling para meters for axial scanning also a number of images per rotation. 17. A method for generating an image in a scalable multi-section computer tomography system ( 10 ) with the steps
Performing a scan based on at least one selected scan parameter and
retrospectively reconstruct an image using the stored scan data and based on at least one selected image reconstruction parameter. 18. The method of claim 17, wherein the sampling parameter ter comprises a first section thickness, and wherein the image recon structuring parameters includes a second section thickness. 19. The method of claim 17, wherein the first cut thickness differs from the second section thickness. 20. The method of claim 17, wherein the sampling parameter ter includes a table speed. 21. The method of claim 17, wherein the sampling parameter a high image quality for the spiral scanning Includes scan mode.   22. The method of claim 17, wherein the sampling parameter a high-speed sensor for Includes scan mode. 23. The method of claim 17, wherein the sampling parameter ter for the spiral scanning a scanning speed and / or a high image quality scan mode and / or one High speed scanning mode included. 24. User interface in a scalable multi-section computer tomography system ( 10 ) in order to enable a user to select at least one scalable scanning parameter and at least one scalable image reconstruction parameter. 25. The user interface of claim 24, wherein the Slicing parameters for cutting thicknesses for multiple cutting Samples included. 26. The user interface of claim 24, wherein the Sampling parameters for a helical scan a scanning speed ability includes. 27. The user interface of claim 33, wherein the Scanning parameters for a helical scan a high Image quality scanning mode included. 28. The user interface of claim 24, wherein the Scanning parameters for a helical scan of a high speed intensity scanning mode.   29. The user interface of claim 24, wherein the Sampling parameters for a helical scan a scanning speed speed, a high image quality scanning mode and a high speed sensing mode. 30. The user interface of claim 24, wherein the Scanning parameters for axial scanning are also a number of images per rotation. 31. The user interface of claim 24, wherein the Image reconstruction parameters includes a section thickness. 32. Method for generating an image in a scalable multi-section computer tomography system ( 10 ) with the steps
Performing a scan based on at least one selected scan parameter,
Capture multi-slice scan data by performing a scan based at least in part on the scan parameter and
retrospectively reconstruct an image using the stored scan data and based on at least one selected image reconstruction parameter. 33. The method of claim 32, wherein retrospectively reconstructing an image comprises the steps
Reconstruct images according to a first anatomy area according to a first image reconstruction parameter and
Reconstruct images according to a second anatomy area according to a second image reconstruction parameter. 34. The method of claim 33, wherein the first image re construction parameters a first section thickness and the second Image reconstruction parameter is a second section thickness. 35. The method of claim 34, wherein the first cut thickness and the second section thickness are different from each other are.